System and Method for Reducing Angular Geometric Distortion in an Imaging Device

ABSTRACT

A system and method are provided for significantly reducing or substantially eliminating angular geometric distortions in devices designed for imaging and/or inspection of an interior portion or surface of a cavity. A series of processing steps or methods may be employed to eliminate Non-Uniform Rotational Distortion (NURD) in such devices, for example, unidirectional and bi-directional intravascular ultrasonic (IVUS) imaging systems. The system may include a processor and an electronic module which control operation of a transducer assembly provided at a distal end of a catheter assembly. The system invokes a first processing step or method to collect and store raw angle and line data, as well as one or more of second and third processing steps or methods which adjust for NURD experienced during backlash of a bi-directional imaging system and a fourth processing step or method which performs a line-to-line correlation function.

BACKGROUND OF THE INVENTION

1. Field of the Invention

This invention relates to a system and method for reducing angulargeometric distortion in an imaging device.

2. Background of the Related Art

A number of diagnostic tools are used in the field of InterventionalCardiology to diagnose and treat heart disease. Among other things,Intravascular Ultrasonic (IVUS) imaging systems are used to estimate anextent of coronary artery plaque, allowing an interventionalist todetect heart disease, estimate the severity of the disease and itseffect on blood flow, and choose appropriate therapies. One such systemis a fluoroscopy system, which injects a radio-opaque contrast dye intothe bloodstream, and then uses a real time x-ray imaging technique towatch as the contrast dye passes through the vascular tree. However,fluoroscopy systems do not image the vessel tissue, but rather the bloodpool inside the vessel lumen.

In an attempt to obtain an image of the vessel wall, and not just theblood pool, ultrasonic imaging transducers are mounted at the distal endof catheters and positioned in the coronary arteries. This approachallows the visualization of the tissues of the artery walls, and moreparticularly, visualization of the atherosclerotic plaque that forms inthese vessels. However, these images are compromised in that the assumedangular orientation of the ultrasonic transducer at the distal tip ofthe catheter is not, in fact, the actual orientation of the transducer.

More particularly, in many IVUS imaging systems, the proximal end of atorque cable is spun at a uniform velocity by an electric motor. Forexample, a motor rotated at approximately 1800 RPM generates a completecircular cross section at a rate of approximately 30 frames, or images,each second. However, a catheter has a number of bends and twists in itslength necessary to get from the entry point into the human body to apoint at which an image is acquired. One of the most common distortionsgenerated by these types of IVUS systems is Non-Uniform RotationalDistortion (NURD).

NURD can be caused by a number of different sources, including, forexample, friction between the spinning torque cable and the stationarysheath that encloses the cable, or the torque cable and transducerassembly being not perfectly cylindrically symmetrical, causing thecable to resist bending more at some angles than at other angles. Whenrotated, these asymmetries will cause the cable to store more energy insome angular orientations and then to release that energy as the cableis rotated past that angle. In either case, the angular velocity of thetransducer varies with each cycle even if the motor maintains a constantspeed at the proximal end of the catheter. In many situations, anabsolute angular orientation of a particular lesion or section of alesion may be critical in performing an accurate, timely diagnosis andprescribing appropriate treatment. Thus, it is important tosubstantially eliminate, or at least significantly reduce, NURD so thatthese measures of angular extent are accurate and reliable.

To this end, new IVUS systems have been proposed in which the catheteris manually rotated in either direction so as to produce an image of asector of an artery, rather than spinning the catheter in a singledirection. However, this change in rotational direction leads to anotherform of NURD caused by the “windup” and resulting “backlash” of thetransducer when the rotational direction is changed. Electronicallysteered imaging systems produce images without rotating the transducerson the distal end of the catheter, and thus do not produce anyrotational distortion. However, this comes at the expense of increasedtransducer, catheter, and imaging system complexity and cost.

SUMMARY OF THE INVENTION

An object of the invention is to solve at least the above problemsand/or disadvantages and to provide at least the advantages describedhereinafter.

Embodiments of the invention are directed to a system and method forreducing angular geometric distortion in an imaging device. The systemand method according to the invention may be utilized with any type ofdevice used to image and/or inspect an interior portion of a cavity,such as a substantially tubular cavity, in which it is advantageous tosignificantly reduce or substantially eliminate angular geometricdistortion.

Further, embodiments of the invention are directed to a system andmethod capable of significantly reducing or substantially eliminatingNURD in both continuously rotated IVUS systems, in which the directionof rotation remains substantially constant, and in manually rotated IVUSsystems, in which the direction of rotation is changed and windup andbacklash NURD are also present.

Additional advantages, objects, and features of the invention will beset forth in part in the description which follows and in part willbecome apparent to those having ordinary skill in the art uponexamination of the following or may be learned from practice of theinvention. The objects and advantages of the invention may be realizedand attained as particularly pointed out in the appended claims.

BRIEF DESCRIPTION OF THE DRAWINGS

The invention will be described in detail with reference to thefollowing drawings in which like reference numerals refer to likeelements wherein:

FIG. 1A is an exemplary IVUS imaging system by means of whichembodiments of the invention may be implemented;

FIG. 1B is a block diagram of a processor according to an embodiment ofthe invention;

FIG. 2 is an exemplary data table generated and stored by the processorshown in FIG. 1B;

FIGS. 3A-3G are flow charts which show a number of differentcombinations and sequences of processing steps or methods which may beimplemented in the exemplary IVUS imaging system shown in FIG. 1A and/orimplemented by the processor shown in FIG. 1B;

FIG. 4 is a flow chart of a process to collect raw angle and echo linedata such as that shown in FIG. 2, in accordance with an embodiment ofthe invention;

FIG. 5 is a flow chart of a backlash and/or windup NURD removal process,in accordance with an embodiment of the invention;

FIG. 6 is a flow chart of an angular correlation process, in accordancewith an embodiment of the invention;

FIG. 7 is a flow chart of a line-to-line correlation process, inaccordance with an embodiment of the invention;

FIG. 8A is a flow chart of a data table rewriting process, in accordancewith an embodiment of the invention; and

FIG. 8B is a flow chart of a data table rewriting process, in accordancewith an embodiment of the invention.

DETAILED DESCRIPTION OF PREFERRED EMBODIMENTS

The following detailed description of embodiments of the invention isdiscussed in the context of NURD reduction for an IVUS system. However,the invention may be utilized with any type of device used to imageand/or inspect an interior portion of a cavity, such as a substantiallytubular cavity, in which it is advantageous to significantly reduce orsubstantially eliminate angular geometric distortion.

NURD reduction for an IVUS system can be viewed as a process that moreaccurately assigns angles that are associated with each acoustic line inan IVUS frame compared to angles that are assumed to be present at aproximal end of a catheter as imaging data is collected. The systems andmethods according to certain embodiments of the invention applyalgorithms which may be implemented in either hardware or software, andmay operate in real time on data as it is collected from a transducer toproduce images without any objectionable distortions caused by NURD.

It should be noted that, as discussed above, medical devices, and moreparticularly, IVUS devices, are referred to herein merely for ease ofdiscussion, and that the systems and methods according to embodiments ofthe invention may be applied to any device used to image and/or inspectan interior portion of a cavity, such as a substantially tubular cavity,to significantly reduce or substantially eliminate angular geometricdistortion. Further, although the term “IVUS system” refers toultrasonic imaging systems, the systems and methods apply as well toother forms of intravascular imaging systems, such as, for example,those that use other forms of energy to make images. These systems mayinclude, for example, optical imaging systems, such as, for example,Optical Coherence Tomography.

FIG. 1A illustrates an exemplary IVUS imaging system by means of whichembodiments of the invention may be implemented. The system 1 of FIG. 1Aincludes a processor 20 which controls an electronics module 18. Theelectronics module 18 transmits an ultrasonic pulse to a transducerassembly 14 positioned at a distal tip 28 of a catheter 10 via data apath 12, and an angle encoder 16 records the relative angle of thecatheter and transmits it back to the electronics module 18. Incrementalangle information sensed by the angle encoder 16 is transmitted to theelectronic module 18 via a data path, or cable 22, and a data path, orcable 24 provides the power and ground for the angle encoder 16. Echodata is returned to the electronics module 18 via the data the path 22,and the processor 20 accepts the echo digitized data from theelectronics module 18 and stores it in a data table, such as theexemplary data table shown in FIG. 2. Software running in the processor20, or alternatively, hardware or firmware running in the electronicsmodule 18, manipulates the information in the data table to remove theNURD artifact and an intravascular image is then created by scanconversion of the information in the data table and displayed on adisplay module 21. In some embodiments of the invention, the processor20 may be a separate unit, as shown in FIGS. 1A-1B, while in otherembodiments of the invention, the capabilities of the processor 20 maybe included in the electronics module 18.

FIG. 1B is a block diagram of a processor in accordance with anembodiment of the invention. The processor 520 may be implemented, forexample, by software provided in processor 20 of FIG. 1A or by hardwareor firmware provided in electronics module 18 of FIG. 1A. The processor520 of FIG. 1B includes a data collection processor unit 530 and one ormore of a backlash and/or windup NURD removal processing unit 540, anangular correlation processor unit 550, and a line-to-line correlationprocessor unit 560. The processor units 540, 550, and 560 may all beprovided and used as needed to significantly reduce and/or substantiallyeliminate NURD based on the application and/or the desired correction.Alternatively, one or more of the processor units 540, 550, and 560 maybe eliminated, for example, to reduce costs or processing time based onthe application and/or the desired correction.

The data collection processor unit 530 functions to collect raw data,including angle and echo line data. The raw data may be stored in a datatable, such as the exemplary table shown in FIG. 2 and further discussedbelow. For example, the data collection processor unit 530 may implementthe methodology discussed below with respect to FIG. 4 of the presentapplication. However, other data collection methodology may also beutilized.

The backlash and/or windup NURD removal processor unit 540 functions toremove NURD caused by backlash in the catheter when the direction ofrotation is changed and a fixed amount of windup NURD is assumed to bepresent in a given imaging situation. For example, the backlash and/orwindup NURD removal processor unit 540 may implement the methodologydiscussed below with respect to FIG. 5 of the present application.However, other methodologies capable of removing NURD caused by backlashin a catheter when the direction of the rotation is changed and a fixedamount of windup NURD is assumed to be present in a given imagingsituation may be utilized.

The angular correlation processor unit 550 functions to remove backlashNURD by performing an angular correlation on the collected data. Forexample, the angular correlation processor unit 550 may implement themethodology discussed below with respect to FIG. 6 of the presentapplication. However, other methodologies capable of removing backlashNURD by performing an angular correlation on the data collected may beutilized.

The line-to-line correlation processor unit 560 functions to calculate across-correlation between adjacent data lines and then discard redundantlines. For example, the line-to-line correlation processor unit 560 mayimplement the methodology discussed below with respect to FIG. 7 of thepresent application. However, other methodologies capable of calculatinga cross-correlation between adjacent data lines and then discardingredundant lines of data may be utilized.

As discussed above, embodiments of the invention may be implementedusing a plurality of processing steps in various combinations. Suchplurality of processing steps or methods include collecting raw angleand echo line data, which may be stored in a data table, such as thatshown in FIG. 2, removing backlash and/or windup NURD, performingangular correlation on the collected data and discarding redundant data,and performing line-to-line cross-correlation and discarding redundantlines of data. Each of these processing steps or processes will bediscussed in more detail below. The processing steps may be used invarious combinations to significantly reduce and/or substantiallyeliminate NURD, based on the application, for example, the particularimaging system utilized, and/or the desired correction. FIGS. 3A-3G showvarious exemplary combinations of the process steps, as discussed below.

FIG. 3A is a flowchart of an exemplary arrangement of processing methodsor steps in accordance with an embodiment of the invention. First, imagedata is collected in step S100 and then NURD is reduced through theremoval of redundant data using known backlash data (S200), performingangular cross-correlation (S300), and performing line-to-line crosscorrelation (S400). Each of the NURD reducing processing steps canreduce NURD depending on the source of the NURD and the particularimaging system used. Further, each of the NURD reducing processing stepscan also be used as standalone processing steps as necessary to, forexample, reduce processing time and/or system cost. The steps whichremove backlash/windup NURD (S200, S300) may be utilized with IVUSsystems which change rotational direction, while the line-to-linecorrelation processing step (S400) may be applied to both unidirectionaland bi-directional systems. Although the processing steps are all shown,sequentially, in FIG. 3A, any number of combinations and/or sequences,such as, for example, those illustrated in the flow charts shown inFIGS. 3B-3E, may be applied to significantly reduce and/or substantiallyeliminate NURD in an IVUS system, depending on the application or systemused, and the desired correction or results.

The processing steps may be considered successive manipulations ofinformation contained in a data table such as, for example, the datatable shown in FIG. 2. In some IVUS systems, a line rate, or datacollection rate, is fixed, while the number of lines in an image isvariable, and the number of lines then depends on a somewhat variablecatheter rotation rate. Consequently, the number of lines in a datatable for such a system is also variable. In contrast, in other IVUSsystems, the number of acoustic lines is fixed, and the line rate variesbased on an angular velocity of the catheter. The processing steps canbe applied to either type of IVUS system in a number of different ways,including, for example, a software algorithm, firmware controlling aField Programmable Gate Array (FPGA), an Application Specific IntegratedCircuit (ASIC), a pipeline processor implemented totally in hardware, ora combination of one or more of these.

Each of the processing steps will now be discussed in more detail.

FIG. 4 is a flow chart of the data collection processing step or method(S100) shown in FIGS. 3A-3G. The data collection processing step simplycollects angle and echo line data. The data may be stored in a datatable, such the exemplary data table 50 shown in FIG. 2. The length ofthe data table may be established based on the amount of memoryavailable. Further, the data table may contain all of the acoustic echolines from a few revolutions of a catheter in a motor driven,unidirectional IVUS system, or 10 to 15 direction reversals in amanually rotated, bi-directional IVUS system. The data collectionprocessing step builds the initial raw data table of angles andassociated image lines. It is well understood that the line data thatrepresents the returned echoes from a constantly increasing radius ordepth is, in fact, an array. However, for ease of discussion, each lineof information will be treated as if it is a simple scalar rather thanan array.

Referring again to FIG. 1A, ultrasound scanning is initiated byelectronics module 18 with the transmission of a pulse of sound to thetransducer assembly 14. Echoes are returned to the transducer assembly14 from the acoustic impedance discontinuities encountered by the pulsein the tissue being interrogated, and are processed into a time seriesof discrete samples. This can be accomplished in a number of ways,including, for example, by digitizing the returning radio frequencysignal directly, or by mixing it down to an intermediate or basebandfrequency, or by detecting the information and digitizing the detectedsignal. In any case, the sampling rate is preferably consistent with theNyquist criteria of at least twice the bandwidth of the signal to besampled. It is preferable to digitize the detected data to minimize thenumber of sampled points in an echo line.

For example, for a ˜40 MHz center frequency transducer with a ˜60%fractional bandwidth, the information bandwidth of the amplitudemodulated signal is ˜24 MHz. According to the Nyquist criteria, thissignal must be sampled at least ˜48 million times each second. If, forexample, a ˜50 MHz sampling rate is used, and it is desired to collectan echo line of ˜10 mm in length, then the number of samples in the echoline is:

$\begin{matrix}\begin{matrix}{{EchoLineSamples} = \frac{{Line}\mspace{14mu} {Length}*{SamplingRate}}{\left( {{Speed}\mspace{14mu} {of}\mspace{14mu} {Sound}\mspace{14mu} {in}\mspace{14mu} {{Water}/2}} \right)}} \\{= \frac{10\mspace{14mu} {mm}*48\mspace{14mu} {{samples}/\mu}\; \sec}{1.5\mspace{14mu} {{mm}/\mu}\; {\sec/2}}} \\{= {623\mspace{14mu} {samples}}}\end{matrix} & \left( {{Eqn}.\mspace{14mu} 1} \right)\end{matrix}$

The number 2 in the denominator of Equation 1 reflects the fact that thesound must travel to the point of interest, and the echo must returnfrom that point to the transducer, effectively progressing at half thespeed of sound in the tissue. Along with the echo data, the proximalangle for each scan line at the time of pulse transmission is recordedby the electronics module 18.

Each time the data collection processing step is invoked, incoming pairsof proximal angle and echo data are used to construct a new version ofthe data table. As previously discussed, the data table may contain alist of angles and the echo data that is captured at each particularangle. For ease of discussion, the exemplary data table shown in FIG. 2is represented as an array with three columns and “N” rows. The firstcolumn serves as an array index “n” which is an ordered integer from 1to “N” where “N” is the number of rows (i.e. proximal angle/scan linepairs) obtained. The second column is the Angle(n) and the third columnis the EchoData(n,t). Each entry in the EchoData column is a time seriesor array of discrete samples. The time values start from the moment thetransmit pulse occurs until the last echo of interest is returned fromthe maximum depth to be displayed in the image. These time valuescorrespond linearly with distance or depth from the face of thetransducer.

The number of rows “N” in the data table may be a function of a numberof design considerations. In general, a shorter data table results in ashorter overall latency period through all of the processing steps.Input data sets as short as one proximal angle/echo data pair areallowed. This yields a data table size of N=2 due to the optionalbuffering of the last line from one iteration of the data collectionprocessing step to the next; this configuration supports pipelinedoperation in which data flows continuously through all processing steps.The determination of the end-of-input-data condition includes, but isnot limited to, the following conditions:

1. A predetermined number of scan lines have been received (1 . . . N).

2. A predetermined number of complete 360° image frames have beenreceived (1 . . . F).

3. A predetermined time interval has elapsed.

4. A predetermined number of direction reversals have occurred (1 . . .R).

5. A predetermined time of no input activity has occurred.

As shown in FIG. 4, a line counter is initially set to 1, in step S110,and the counter is increased by 1, in step S115, as the data iscollected and stored. The method determines if the end of input data hasbeen reached, in step S120, based on the criteria set forth above. Ifthe end of input data has been reached, the last line in the data table150 is saved to the last line buffer 117, in step S155, and the datatable 150 is sent to the next processing step, or for scan conversion,as appropriate, in step S160. If the end of input data has not beenreached, the proximal angle(n) is obtained, in step S125, and written tothe data table 150, in step S130, and scan line echo data(n) isobtained, in step S135, and written to the data table 150, in step S145.The counter is then increased by 1, in step S145, and the processrepeats until the end of input data is reached, in step S120.

FIG. 5 is a flow chart of the backlash and/or windup NURD processingstep or method shown in FIGS. 3A-3C and 3F. This processing step senseswhen the catheter has reversed its rotational direction, and removes thelines corresponding to a predetermined minimum backlash angle from thedata table. The remaining lines are then rotated by the predeterminedbacklash angle to remove the angular distortion. An estimate of theminimum amount of backlash that will always occur upon a change ofrotational direction for any particular imaging situation ispredetermined and loaded into an a priori backlash data table. Manyfactors influence these backlash angles, including, for example, thetype of guide catheter used, the access site to the patient, theguidewire employed, a patient body type, and other such factors whichhave had their minimum backlash angles experimentally measured for eachof the catheters that may be compatible with a particular imaging systembeing used. This processing step can be used with a catheter that canimage while being rotated in both directions, i.e., a bi-directionalIVUS system.

When the rotational direction is reversed, the distal tip of thetransducer is assumed to be stationary until the minimum backlash anglehas passed at the proximal end of the catheter. The backlash angle is,for purposes of discussion, assumed to be the total angle necessary tounwind any twist in the catheter added to the angle necessary to rewindthe catheter in the opposite direction so as to start the distal tipmoving again in the opposite direction. After the proximal end of thecatheter has exceeded the backlash angle, the method begins writinglines according to the incremental angles measured at the proximal end.Conceptually, the best case backlash scenario occurs when the catheteris held as straight as possible with no bends other than those createdby the guide catheter. All other scenarios will typically have morebacklash since, in general, more friction will be present due to thecatheter being forced to bend by contact with the vessel wall. Sinceguide catheters of various shapes are typically used with IVUS imagingsystems, putting the IVUS catheter inside the guide catheter andmeasuring the backlash when there is no load on the part of the catheterthat extends distal to the tip of the guide catheter, or the part thatis proximal to the proximal end of the guide catheter, will be areasonable best case minimum backlash measure.

As discussed above, the backlash/windup NURD removal processing step ormethod acts to remove NURD caused by backlash in the catheter when thedirection of rotation is changed. This fixed amount of windup NURD isassumed to be present in a given imaging situation. The a prioribacklash data table may provide measured, estimated, or calculatedbacklash data for a variety of combinations of guide catheter-IVUScatheter combinations, and allows this processing step to significantlyor completely remove the minimum amount of NURD that will always occurfor any one of the combinations available.

In the method of FIG. 5, the a priori backlash data table 212 and thedata table 250 are made accessible as the method is initialized, in stepS210, and a processing loop is entered where the lines in the data table250 are examined, in steps S215, S220. A rotational direction change isidentified, in step S225, when the catheter angles in the data table 250go from monotonically increasing to monotonically decreasing, orvice-versa. If no direction change has occurred, no change to the datatable 250 is made, and the next angle in the data table 250 is examined,in step S215, until the end of the data table 250 is reached, in stepS230.

However, when a direction change has occurred, in step S225, the datatable 250 is rewritten to remove all of the angles and echo data linesthat are contained within a preset backlash angle, in step S227. All ofthe data table 250 entries in the intervening backlash angle areremoved, and the angles for all subsequent rows in the data table 250are adjusted, in step S227, by subtracting or adding the preset backlashangle from the a priori backlash data table 212, plus the currentadjustment angle 229 from the original angle depending on whether thedirection change was from clockwise to counterclockwise, or fromcounterclockwise to clockwise.

Referring again to the system shown in FIG. 1A as an example, thisassumes that the transducer assembly 14 at the distal end 28 of thecatheter 10 will be stationary after the change in direction, but beforethe complete backlash angle has been subtended, so echo data for all ofthe lines in the intervening backlash angle will be nearly identical.The backlash/windup removal processing step is computationally verysimple and its implementation is inexpensive either from a parts cost ora computer processing time perspective. As such, it could eliminate thebacklash lines without the expense of the additional computer cyclesrequired for the angular or line-to-line correlation steps. If theline-to-line correlation processing step or the angular correlationprocessing step is employed in addition to the backlash/windup removalprocessing step, then it is preferable that the backlash/windup removalprocessing step precede either or both of the other two steps. Moreparticularly, the line-to-line correlation step and the angularcorrelation step will remove the redundant lines in the backlash anglebecause they will be highly correlated. The backlash/windup removalprocessing step would then simply sense the change in direction andremove an additional set of lines that would in fact be valid data thatis not redundant. It can, however, be desirable to have the backlashremoval processing step employed in conjunction with the otherprocessing steps because it is a more efficient way to remove thatbacklash artifact, thereby saving computer cycles for other things, suchas, for example, scan converting the acoustic lines into images,monitoring and responding to the human interface, and any signalprocessing tasks that the system employs.

After all of the rows in the incoming data table have been processed, instep S230, the modified data table can be sent to the next processingstep for further NURD reduction, or sent to be scan converted anddisplayed, in step S235. The current adjustment angle 229 is updated byadding or subtracting the backlash angle and retained for the nextinvocation of the backlash/windup NURD removal processing step.

FIG. 6 is a flow chart of the angular correlation processing step ormethod shown in FIGS. 3A, 3C-3D, and 3G. Like the backlash/windup NURDremoval processing step, this processing step senses a reversal in thedirection of rotation. The process then calculates an angularcross-correlation between sectors that occur before and after thedirection change. This may be, for example, complete 360-degree images,or sectors of images, and the same processing step may be applied whenchanging from clockwise to counterclockwise rotation as when changingfrom counterclockwise to clockwise rotation. The angle that produces themaximum of the angular cross-correlation is used to rotate the imagesector so as to properly align the two images sectors without theintervening backlash. In this case, angle values in the data table areshifted by the angle that corresponds to the maximum cross-correlationangle, while the echo data remains unchanged.

The angular correlation processing step may follow the backlash/windupNURD removal processing step, or may be used immediately following thedata collection processing step. When used subsequent to thebacklash/windup NURD removal processing step, the angular correlationprocessing step removes any remaining backlash that occurs in additionto the minimum that was stored in the a priori backlash data table. Thisadditional backlash angle is a consequence of the less than idealcircumstances that were measured, estimated, or calculated in the apriori backlash data table. For example, higher catheter rotationvelocity, more total bending of the catheter as it accesses the desiredvasculature, and contact with the vessel walls after exiting the guidecatheter all cause more frictional drag and, consequently, morebacklash. The angular correlation processing step may be carried out onthe raw data in the data table, or the acoustic lines can be moved tothe nearest display line and the intervening pixels left uncalculated

As set forth above, the angular correlation processing step aligns thesectors of an image just prior to and subsequent to a change in catheterrotation direction. As shown in FIG. 6, a loop index “k” is initiallyset to zero, in step S310, the loop index “k” is incremented for eachchange in catheter rotation direction, in step S315, and a rotationaldirection change is detected, in step S320, as discussed in more detailwith respect to FIG. 8A. Once the direction changes are located in thedata table 350, Sector_(k), which represents the set of rows thatrepresent the image information a set amount before the change indirection and Sector_(k+1) which represents the image information a setamount after the change in direction can be determined, in steps S320,S325, and S330. For ease of discussion, forty degrees is chosen as theset amount, as a 40 degree sector angle would provide sufficient imagearea to provide a robust angular cross-correlation but is small enoughso that an operator who may be manually sweeping out the image wouldsweep through the entire sector angle in normal practice; however, othersector angles may also be appropriate. This corresponds to the numericalintegration from −20 degrees to +20 degrees in Eqn. 2. This angle can bea predetermined number stored in a table much like the a priori backlashdata table discussed above, and may represent an optimum angle dependingon any particular imaging situation that can be known in advance.

The 40 degree sector just prior to a catheter rotational directionchange is compared to the 40 degree sector subsequent to the directionchange, and the rotation angle necessary to align these two sectors iscalculated, in step S335, based on an angular cross-correlation formulashown below in Equation 2. Preferably, the angular cross correlation isperformed on the “pre-scan-converted” lines in the data table with theangular position of the acoustic lines rounded to the nearest displayline. Once the angular cross-correlation has been calculated, in stepS335, the actual angles are used for scan conversion purposes.

$\begin{matrix}{{{{AC}_{k}(\theta)} = {{{Sector}_{k}(\theta)}{{Sector}_{k + 1}(\theta)}}}{{{AC}_{k}(\theta)} = {\sum\limits_{\alpha = {- 20}}^{20}{{{Sector}_{k}(\alpha)} \times {{Sector}_{k + 1}\left( {\alpha - \theta} \right)}}}}} & \left( {{Eqn}.\mspace{14mu} 2} \right)\end{matrix}$

-   -   Where: AC_(k) (θ) is the Angular-Correlation as a function of        the offset angle θ, the angle θ is allowed to vary over + and        −20 degrees, and α is the angular index over which the        correlation is integrated.        It will be obvious to one skilled in the art that this        calculation is in fact a summation over as much as 80 degrees of        image data.

The angular cross-correlation function in Equation 2 will have a maximumvalue θ_(MaxAC(k)) for the angular rotation (θ) that best aligns the twosectors of the IVUS image. Once the angular cross-correlation iscalculated, in step S335, the maximum of the function is determined, instep S340, Sector_(k+1) is rotated by that angle, and the data table 350is rewritten to remove redundant lines and adjust the remaining angles,in step S345. The rotation of the sector involves only the addition ofthe θ_(maxAC(k)) value, plus the current adjustment angle 355, to theAngle(n) column for the EchoData(n) line that marks the beginning ofSector_(k+1) through the end of the data table 350.

Once the angles in the data table 350 have been rewritten, in step S345,if the end of the data table 350 has not been reached, in step S360, theloop index “k” is incremented, in step S315, the next change indirection is found, in step S320, and the process repeats until the lastdirection change has been processed. When the last direction change hasbeen processed, the data table 350 is ready to be sent to the nextprocessing step or scan-converted and displayed, in step S365. Thecurrent adjustment angle 355 is updated by adding in the net sum of allthe θ_(MaxAC) for all the sectors in the data table and retained for thenext invocation of this processing step.

FIG. 7 is a flow chart of the line-to-line correlation processing stepor method shown in FIGS. 3A and 3E-3G. This processing step isapplicable whether the catheter is unidirectional or bi-directional, andis used to calculate a cross-correlation between adjacent lines. If thecross-correlation is above a preset threshold, it is assumed that thedistal end of the transducer assembly is substantially stationary, thatthe lines are taken from the same angular location, and therefore one ofthem is redundant and should be discarded. This is considered to be aNURD sector of the IVUS image, and would likely show up as a “streaked”sector where the lines have the same echo pattern for many differentapparent angles. Thus, all but the first or last line are discardeduntil the correlation coefficient drops below the preset threshold. Areduction in the cross-correlation indicates that the transducer isagain rotating and presumably tracking the proximal angle encodervalues, and the image lines are written accordingly. With a frame bufferand sufficient line density, the changing lines at either edge of thesector which would have been “streaked” (i.e. the NURD sector) can berepositioned across the (to be discarded) highly correlated sector toreduce the geometric distortion.

This processing step can assume that the transducer is moving at aconstant velocity when the line-to-line correlation coefficients are nolonger approximately one. Further, it may be assumed that the transducerwill accelerate before reaching a certain velocity that it will maintainuntil either the drive on the proximal end is changed or theline-to-line correlation again approaches one. Similarly, for the linesjust preceding the NURD sector where the lines are highly correlated, itmay be assumed that the transducer decelerates to zero angular velocityat the edge of the leading edge of the NURD sector. Either of thesecorrections allows a more accurate geometric presentation of thereceived data than the constant velocity assumption that is implicit inconventional mechanically rotated IVUS systems.

The line-to-line correlation processing step may accept the raw datatable from the data collection processing step, and/or may accept thedata table as processed in either the backlash/windup NURD reductionprocessing step and/or the angular correlation processing step. Themethod is initialized, in step S410, and the line number in the datatable 450 is incremented, in step S415. A correlation between adjacentlines is calculated, in step S420. The LineCorr(n) is compared to apredetermined threshold (Th_(o)), in step S430, and if the LineCorr(n)is greater than the predetermined threshold (Th_(o)), these highlycorrelated lines are discarded and the remaining lines are reoriented,in step S435. The process is repeated until the end of the data table450 is reached, in step S440, and the data table 450 is ready for scanconversion and/or display, in step S460. The formula for theline-to-line correlation calculation, in step S420, is shown in Equation3.

$\begin{matrix}\begin{matrix}{{{LineCorr}(n)} = {{{EchoData}\left( {n,i} \right)}{{EchoData}\left( {{n + 1},i} \right)}}} \\{= {\frac{1}{\left( {{EchoLineSamples} - 1} \right)} \times}} \\{{\sum\limits_{i = 1}^{EchoLineSamples}{{{EchoData}\left( {n,i} \right)} \times {{EchoData}\left( {{n + 1},i} \right)}}}}\end{matrix} & \left( {{Eqn}.\mspace{14mu} 3} \right)\end{matrix}$

This correlation value would typically be between 0.90 and 1.00 if thetwo lines were received while the transducer, at the distal end of thecatheter, was in substantially the same position. However, it is notexactly 1.00, because there is always some level of thermal noise in thereceiver and the transducer is never perfectly stationary in a livingsystem due to respiration, heart beat, patient motion, and other suchexternal influences. If the line-to-line correlation coefficient is low,then the adjacent acoustic lines represent substantially independentacoustic lines. Equation 3 can be implemented on the EchoData signalsafter the DC component has been removed (AC coupled) or with the DCcomponent intact with similar results.

The correlation coefficient, LineCorr(n), for the n^(th) acoustic lineand the n+1^(st) acoustic line is then compared to a preset thresholdvalue (Th_(o)) of for example, 0.95, in step S430. If the correlationbetween the lines exceeds the preset threshold (Th_(o)), then it isassumed that the transducer is not moving during the time the two lineswere acquired, one of the lines is discarded, and the data table 450 isrewritten accordingly, in step S435. The process of re-writing the datatable 450 is discussed in more detail with respect to FIGS. 8A-8B. Ifthe correlation between the lines is less than the preset threshold(Th_(o)), in step S430, then the lines are assumed to be valid lines,substantially without NURD, and the next pair of lines is examined. Whenall of the lines in data table 450 have been processed, in step S440,the data table 450 may be sent to another processing step, orscan-converted and displayed, in step S460. The current adjustment angle445 is updated, by adding in the net angle of image sector data removedand angle of the image sector data retained for the next invocation ofthis processing step.

FIGS. 8A-8B are flow charts illustrating data table rewriting processes.The basic difference in these two processes is in the assumptions thatare made for the correct replacement of remaining lines after aberrantlines have been removed. In the event of NURD caused by backlash duringa direction reversal, it is assumed that the distal tip of the catheterwas stationary during the backlash angle. Once the backlash angle isexceeded, the distal tip moves at the same angular velocity as theproximal end of the catheter, thus causing the sector of image thatoccurs after the change in rotational direction to be discarded as thecatheter traverses the backlash angle, and the remaining angles in thesector to be adjusted to rotate the image accordingly.

In contrast, when there is no change in rotational direction, it isassumed that the distal tip of the catheter decelerates just prior tothe occurrence of NURD, remains substantially stopped during the NURDsector, and accelerates just subsequent to the NURD sector. Although,for ease of discussion, it is assumed that the deceleration andacceleration are approximately of the same magnitude and duration, thisis not a necessary condition, as the acceleration and decelerationprofiles may be stored in a table, and may reflect any profile that theactual catheter is likely to experience. In this situation, theremaining lines may be repositioned prior and subsequent to the NURDsector to fill in the gap of discarded lines, and subsequent data tableswill have their initial angle adjusted to reflect the cumulative anglesand lines removed from previous versions of the data table. Thiscumulative angle adjustment from sector to sector, or from data table todata table, is referred to as current adjustment angle.

FIG. 8A is a flow chart illustrating a data table rewriting processinvoked by either of the backlash/windup NURD removal processing step orthe angular correlation processing step. The direction change counter“k” is initialized, in step S805, and angles for pairs of adjacent linesare examined, in step S810, to determine if the rotational direction haschanged, in step S820. If not, the search for a change in directioncontinues as step S810 is repeated. If a direction change is found, instep S820, the index “k” is incremented, in step S830, and the NURDlines are deleted according to the algorithm in either thebacklash/windup NURD removal processing step or the angular correlationprocessing step, in step S840. The sector is then rotated again by anangle specified in the appropriate algorithm, in step S850. This processcontinues until the entire data table has been processed, in step S860,and the data table is returned to the appropriate processing step, instep S870.

FIG. 8B is a flow chart illustrating a data table rewriting processinvoked by in the line-to-line correlation processing step when there isno change in rotational direction. This process requires apre-calculated table which dictates how valid lines are to berepositioned to cover a gap left behind by redundant lines, referred toas the acceleration/deceleration profile 900. If the NURD sector isrelatively wide, then the acceleration and deceleration may be spreadover a wider sector of good data. However, if the NURD occurs in only afew lines, then the acceleration and deceleration of the catheter mostlikely occurs over only a few adjacent lines before a constant angularvelocity is restored. The algorithm may include an accumulator to countthe total number of adjacent lines with high correlation coefficientsand then choose an appropriate acceleration/deceleration profile from atwo-dimensional data set that varies each as a function of the number oflines to be discarded. However, for ease of discussion, a simpleone-dimensional table is shown in FIG. 8B.

The method of FIG. 8B is initiated when the line-to-line correlationprocessing step detects adjacent lines with a high correlationcoefficient. This implies that the transducer is likely stationary, andthe proximal end of the catheter is turning at a nearly constantvelocity. First, one of the two adjacent lines is discarded, in stepS910, and an index “i” that starts the deceleration profile isinitialized, in step S920. The deceleration is assumed to occur over agiven number of lines, for example, 10 lines, as shown in the exemplaryacceleration/deceleration profile 900. A small adjustment may be made tothe angle of the line that is 10 lines prior to the discarded line toaccount for the assumed deceleration that occurs prior to the discardedline, in step S930. The index “i” is incremented, in step S940, and alarger angle is subtracted from the next line until the assumeddeceleration brings the transducer angular velocity to substantiallyzero at the location of the discarded line. At this point, a largeincrement followed by decreasing increments are subtracted from theangles of the respective lines until the index is 10 lines away from thediscarded line, in step S950, as the transducer accelerates. Once thefull acceleration/deceleration profile 900, in this example, 10deceleration adjustments and 10 acceleration adjustments have been usedto adjust the data table, in step S950, and the data table is returnedto the line-to-line correlation processing step, in step S960, to searchfor the next redundant line.

Proper implementation of the acceleration/deceleration profile 900 mayalso help ensure precise orientation of a rotating device inserted in acavity as rotation of the device is interrupted to, for example, moreclosely examine and/or remove tissue or plaque from a particularportion, such as may be done when, for example, using an ablation devicein combination with an imaging system, when precise placement iscritical. More particularly, as the imaging device rotates within thecavity and a corresponding image is displayed to an interventionalistfor examination, the interventionalist may choose to interrupt rotationof the device for more close examination and/or to remove or sampletissue at a particular location. However, as discussed above, whenrotation at the proximal end of the device is stopped, the distal end ofthe device may experience some delay before its corresponding rotationis stopped, and thus may continue to rotate for a short period afterrotation at the proximal end is stopped. Without correction using theappropriate acceleration/deceleration profile 900, this delay at theproximal end may result in imprecise, inaccurate positioning of theimaging and/or ablation device.

The invention as embodied and broadly described herein allows NURD to besignificantly reduced, and/or substantially eliminated withoutsignificant increases in system complexity and cost. The resultingsignificant reduction or elimination of NURD provides a more accurate,reliable measure of angular. orientation and image of anomalies observedduring inspection of the vasculature, thus providing more efficientdiagnosis and more appropriate treatment options.

The foregoing embodiments and advantages are merely exemplary and arenot to be construed as limiting the invention. The present teaching canbe readily applied to other types of apparatuses. The description of theinvention is intended to be illustrative, and not to limit the scope ofthe claims. Many alternatives, modifications, and variations will beapparent to those skilled in the art. In the claims, means-plus-functionclauses are intended to cover the structures described herein asperforming the recited function and not only structural equivalents butalso equivalent structures.

1-65. (canceled)
 66. A system for imaging a vessel, comprising: aprocessing system configured to be in communication with a flexibleelongate member having an ultrasound imaging device attached thereto,the ultrasound imaging device configured to rotate in a first directionand a second direction opposite the first direction, the processingsystem configured to: receive imaging data from the ultrasound imagingdevice while the ultrasound imaging device is rotated in the first andsecond directions; and reduce non-uniform rotational distortion (NURD)generated in the received imaging data by performing at least one of:removing backlash NURD that is generated when the rotational directionof the ultrasound imaging device is changed between the first and seconddirections based on backlash NURD data associated with the ultrasoundimaging device; and performing angular correlation to remove backlashNURD that is generated when the rotational direction of the ultrasoundimaging device is changed between the first and second directions. 67.The system of claim 66, wherein the imaging data received by theprocessor from the ultrasound imaging device includes line datacorresponding to each angle of rotation of the ultrasound imagingdevice.
 68. The system of claim 67, wherein the processing system isconfigured to store the angle and corresponding line data in a datatable.
 69. The system of claim 68, wherein the processing system isconfigured to detect changes in the rotational direction of theultrasound imaging device between the first and second directions basedon changes in the angle data contained in the data table.
 70. The systemof claim 66, wherein the flexible elongate member is a catheter.
 71. Thesystem of claim 66, further comprising a display in communication withthe processing system.
 72. The system of claim 66, further comprising anelectronics module configured to be in communication with the ultrasoundimaging device, the electronics module configured to transmit anultrasonic pulse to a transducer assembly of the ultrasound imagingdevice.
 73. The system of claim 72, further comprising an angle encoderin communication with the electronics module.
 74. The system of claim72, wherein the processing system is included in the electronics module.75. The system of claim 72, wherein the processing system is a separateunit from the electronics module.
 76. A system for imaging a vessel,comprising: a processing system configured to be in communication with aflexible elongate member having an optical coherence tomography (OCT)imaging device attached thereto, the OCT imaging device configured torotate in a first direction and a second direction opposite the firstdirection, the processing system configured to: receive imaging datafrom the OCT imaging device while the OCT imaging device is rotated inthe first and second directions; and reduce non-uniform rotationaldistortion (NURD) generated in the received imaging data by performingat least one of: removing backlash NURD that is generated when therotational direction of the OCT imaging device is changed between thefirst and second directions based on backlash NURD data associated withthe OCT imaging device; and performing angular correlation to removebacklash NURD that is generated when the rotational direction of the OCTimaging device is changed between the first and second directions. 77.The system of claim 76, wherein the imaging data received by theprocessor from the OCT imaging device includes line data correspondingto each angle of rotation of the OCT imaging device.
 78. The system ofclaim 77, wherein the processing system is configured to store the angleand corresponding line data in a data table.
 79. The system of claim 78,wherein the processing system is configured to detect changes in therotational direction of the OCT imaging device between the first andsecond directions based on changes in the angle data contained in thedata table.
 80. The system of claim 76, wherein the flexible elongatemember is a catheter.
 81. The system of claim 76, further comprising adisplay in communication with the processing system.
 82. The system ofclaim 76, further comprising an electronics module configured to be incommunication with the OCT imaging device.
 83. The system of claim 82,further comprising an angle encoder in communication with theelectronics module.
 84. The system of claim 82, wherein the processingsystem is included in the electronics module.
 85. The system of claim82, wherein the processing system is a separate unit from theelectronics module.